EP0470235A1 - Apparatus and method for the detection of air in fluid delivery systems. - Google Patents

Apparatus and method for the detection of air in fluid delivery systems.

Info

Publication number
EP0470235A1
EP0470235A1 EP91905285A EP91905285A EP0470235A1 EP 0470235 A1 EP0470235 A1 EP 0470235A1 EP 91905285 A EP91905285 A EP 91905285A EP 91905285 A EP91905285 A EP 91905285A EP 0470235 A1 EP0470235 A1 EP 0470235A1
Authority
EP
European Patent Office
Prior art keywords
infusion
bubble
air bubble
air
unacceptable
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP91905285A
Other languages
German (de)
French (fr)
Other versions
EP0470235B1 (en
EP0470235A4 (en
Inventor
Donald E Bobo Jr
Alan A Figler
Jeffrey L Frank
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Baxter International Inc
Original Assignee
Baxter International Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
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Application filed by Baxter International Inc filed Critical Baxter International Inc
Publication of EP0470235A1 publication Critical patent/EP0470235A1/en
Publication of EP0470235A4 publication Critical patent/EP0470235A4/en
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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M31/00—Devices for introducing or retaining media, e.g. remedies, in cavities of the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/36—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests with means for eliminating or preventing injection or infusion of air into body
    • A61M5/365—Air detectors

Definitions

  • This invention relates generally to medical equipment, and more particularly to a system and methodology for detecting air in a liquid being delivered into a patient.
  • An infusion system for delivering a drug or other liquid into a patient often includes an infusion device that operates to deliver the liquid at an adjustable rate or dosage.
  • the infusion device operates to control the flow of liquid through a flexible tubing or other infusion conduit that extends from an IV bag or other source of the liquid to an IV needle or other cannula inserted in the patient.
  • the infusion device may include microprocessor control circuitry, front panel operator controls, a display, and an alarm, with those things being integrated in a very functional unit designed to improve intravenous drug administration.
  • the infusion device may also include an air detector.
  • a bubble detector it may take the form of an ultrasonic transmitter/receiver pair and related circuitry arranged to sense air bubbles in the infusion conduit.
  • the ultrasonic transmitter and receiver occupy facing positions on opposite sides of the infusion conduit so that ultrasonic energy passes through the infusion conduit in traveling from the transmitter to the receiver.
  • control circuitry stops the infusion pump and activates the alarm.
  • Unacceptable air bubble size may differ, however, and so it would be advantageous to have some way to set that value. Then an operator could select a bubble size most appropriate for a particular infusion situation and that would, among other things, avoid the nuisance alarms accompanying too sensitive a setting. But existing infusion devices often use fixed-length bubble detector schemes so that sensitivity is fixed at some predetermined value such as a three-eighths inch bubble length (i.e., about fifty microliters in some commonly used infusion conduit) .
  • One common configuration includes a transmitter and receiver about five-eighths inch long and circuitry configured to pass one-eighth inch long bubbles while stopping three-eighth inch bubbles.
  • the circuitry can recognize variations in bubble detector output from a predetermined threshold value signifying that air between the transmitter and receiver is interrupting 20% of the five-eighths inch bubble detector length (i.e., a one-eighth inch long air bubble) , to a predetermined maximum value indicating 60% interruption (i.e., a three-eighths inch long air bubble) .
  • the control circuitry stops the infusion pump.
  • infusion device sensitivity to air bubble size is not adjustable.
  • minimum sensitivity i.e., maximum acceptable air bubble size
  • maximum acceptable air bubble size is dependent on the length of the transmitter/receiver pair, a longer transmitter/receiver pair being required to detect longer air bubbles and establish a threshold value much greater than three-eighths inch.
  • changing the transmitter/receiver pair and associated hardware may be quite costly and inconvenient. So, some other way is needed to reduce infusion device sensitivity in order to pass air bubbles up to an unacceptable size that is larger than the fixed threshold value, and perhaps even larger than the limit imposed by the length of the transmitter/receiver pair.
  • This invention solves the problems outlined above by providing an infusion device having control circuitry configured to determine if during the time an air bubble is detected it advances a distance indicative of an unacceptable size. Preferably, that is done with a suitably programmed microprocessor that counts the steps of the infusion pump and compares it with a predetermined .value calculated for the particular infusion device and infusion conduit employed.
  • the infusion device uses a fixed-length bubble detector in a way that can provide reduced sensitivity, and it does so without incurring the cost and inconvenience of modifying the hardware.
  • the infusion device can be configured to enable operator adjustment of sensitivity level using front panel controls.
  • an infusion device constructed according to the invention includes an infusion pump for delivering a liquid through an infusion conduit from a separate source of the liquid into a patient, a bubble detector for detecting the presence of an air bubble in the infusion conduit, and control means responsive to the bubble detector for determining if the size of the air bubble is unacceptable.
  • the control means is configured to determine if during the time the air bubble is detected it advances a distance indicative of the unacceptable size.
  • the control means includes suitably programmed microprocessor circuitry configured to monitor operation of the infusion pump in order to determine the distance the air bubble advances during the time it is detected.
  • the microprocessor In the case of a linear peristaltic infusion pump, for example, the microprocessor counts the steps of the infusion pump as an indication of the distance the air bubble advances and compares it to a value calculated for the particular infusion device and infusion conduit employed. If an unacceptable size is indicated, the microprocessor stops the infusion pump and activates the alarm.
  • a method of detecting an air bubble of unacceptable size in an infusion conduit through which liquid is to be delivered into a patient includes the step of providing an infusion device having an infusion pump for delivering the liquid through the infusion conduit and a bubble detector arranged to detect the presence of an air bubble in the liquid. The method proceeds by determining if during the time the air bubble is detected it advances a distance indicative of the unacceptable size.
  • the step of determining if the air bubble advances a distance indicative of the unacceptable size includes monitoring infusion pump operation, and that may be done with microprocessor circuitry conf gured to count the steps of a linear peristaltic infusion pump.
  • FIGURE 1 of the drawings is a diagrammatic representation of an infusion device constructed according to the invention
  • FIGURE 2 is a diagrammatic representation showing details of an air bubble advancing within the infusion conduit between the ultrasonic transmitter and receiver of the bubble detector;
  • FIGURE 3 is a representation of a plot of bubble detector output showing how it may vary as the infusion pump advances the air bubble;
  • FIGURES A-4C combine to form a flow chart showing the methodology employed to assess air bubble size.
  • Fig. 1 shows an infusion device 10 constructed according to the invention. It operates to deliver a drug or other liquid from a separate source 11 through an infusion conduit 12 to a cannula 13 and into a patient 14. Including some sort of cabinet or other housing depicted in Fig. 1 by the dashed lines 15, the infusion device 10 operates conventionally in many respects and may include many of the features described in U.S. Patent No. 4,648,869 to Bobo, Jr. That patent is incorporated by reference for the details of construction provided.
  • An infusion pump 16 preferably a linear peristaltic infusion pump, functions conventionally in many respects as infusion pump means for delivering the liquid through the infusion conduit 12.
  • control circuitry in the infusion device 10 may be configured to stop the infusion pump 16 and activate an alarm 25 in the event an air bubble of unacceptable size is detected.
  • control circuitry in the infusion device 10 is configured to monitor the distance an air bubble advances in the infusion conduit 12 as an indication of its size. Preferably, that-is done by suitably programming the microprocessor 24 using known programming techniques to perform the steps subsequently described in greater detail.
  • the sensitivity of the infusion device to bubble size (i.e., the unacceptable bubble size threshold) can be set at a selected level.
  • the programming in one embodiment of the invention is so configured that an operator can vary the sensitivity to any of various levels using front panel controls.
  • sensitivity is independent of bubble detector size.
  • the sensitivity of the infusion device 10 i.e., the unacceptable bubble size threshold
  • the control circuitry of .the infusion device 10 monitors the distance the air bubble advances in the infusion conduit 12 as the air bubble is causing certain variations in the output of the bubble detector 17. That distance taken in conjunction with the inside diameter of the infusion conduit 12, provides sufficient information for the control circuitry to assess the length of the air bubble (i.e., determine whether the size of the air bubble is unacceptable) .
  • Fig. 2 is a diagrammatic representation showing the advance of an air bubble 30 (i.e., a column of air) in the infusion conduit 12. Dimensions are exaggerated for illustrative convenience.
  • the air bubble 30 advances between an ultrasonic transmitter/receiver pair that includes an ultrasonic transmitter 31 and an ultrasonic receiver 32 that are components of the bubble detector 17 shown in Fig. 1. They are arranged in a known way so that ultrasonic energy passes through the infusion conduit 12 in traveling from the transmitter 31 to the receiver 32.
  • the air bubble 30 has a forward end 33, a rearward end 34, and a length (Lg) that is the distance between the forward end 33 and the rearward end 34 (Fig. 2).
  • the air bubble 30 can be something other than air, and so it is intended that the term "air bubble” include a column of any other substance that might be detected by the bubble detector 17.
  • the forward end 33 eventually passes to a position between the transmitter 31 and receiver 32 where it causes the bubble detector output to vary in some respect, such as amplitude, from an uninterrupted value indicating that there is only liquid between the transmitter 31 and receiver 32 (point A in Fig. 3) to an air/no-air threshold value indicating the initial presence of the forward end 33 of the air bubble 30 (point B) .
  • That position can be referred to as a first detectable position, and it is illustrated in Fig. 2 by the position occupied by the forward end 33 of the air bubble 30.
  • the air bubble length Lg is less than the bubble detector length L Q .
  • the bubble detector output remains constant to point D where the air bubble begins to pass from between the transmitter 31 and the receiver 32. If Lg were equal to or greater than p, however, the bubble detector output would decrease further to a fully interrupted value less than the value at point C.
  • the bubble detector output begins to increase back to the air/no-air threshold value at point E equal to that at point B. That may be called a second or final detectable position and it is depicted in Fig. 2 by an air bubble 30' in phantom lines. It may occur, for example, when one-eighth inch of the air bubble 30' is still between the transmitter 31 and the receiver 32 as depicted by the dimension in Fig. 2 labelled L ⁇ (the second threshold). Then, as the air bubble 30' passes fully beyond the transmitter 31 and the receiver 32, the bubble detector output increases back to an uninterrupted value at point F equal to that at point A.
  • the bubble detector output varies predictably according to the position of the air bubble 30 between the transmitter 31 and the receiver 32 so that monitoring the distance the air bubble advances from the time the bubble detector output varies from point B to point E in Fig. 3, enables the control circuitry to assess air bubble size.
  • that distance is monitored by counting the steps of the infusion pump 16. Then, the number of steps to occur (labeled "X" steps in Fig. 3) is compared with a predetermined value indicative of an unacceptable bubble length.
  • a periodic timer interrupt used to advance the stepper motor of the infusion pump 16 causes program control to proceed to point 40 in Fig. 4A, the start of a pump interrupt service routine.
  • the program reads the bubble detector output at 41, examines a SENSOR STATE flag at 42 to determine if it is equal to NO-AIR, and if NO-AIR it is not, the program proceeds to point A in Fig. 4B (subsequently described) .
  • the program checks at 43 to see if the bubble detector output is less than the air/no-air threshold level. If it is not, the stepper motor is advanced to the next step at 44 and the program exits the pump interrupt service routine at 45. If the bubble detector output is less than the air/no-air threshold level, the program sets the SENSOR STATE flag at 46 to indicate AIR, advances the stepper motor at 47, and exits the pump interrupt service routine at 48.
  • Fig. 4B the program proceeds from point A to see at 49 if the bubble detector output is less than the air/no-air threshold..,. If . it. is, .the . program checks at 50 to see if the infusion pump 16 is not in the deadband region of the peristaltic pump. If NO, program control proceeds to point B in Fig. 4C. If YES, the program first increments an active region step counter at 51 and then proceeds to point B in Fig. 4C.
  • the program sets the SENSOR STATE flag to equal NO-AIR at 52. Then, it advances the stepper motor to the next step at 53 and exits the pump interrupt service routine 54.
  • the program proceeds from point B to see at 55 if the active region step counter is equal or greater than X (the predetermined number of steps indicative of an unacceptable bubble size) . If YES, the program stops the infusion pump and activates the alarm at 56 and exits the pump interrupt service routine at 57. If NO, the program first advances the stepper motor to the next step at 58 and the exits the pump interrupt service routine at 59.
  • the control circuitry determines whether the size of the air bubble 30 is unacceptable.
  • the control circuitry monitors infusion pump operation for that purpose, counting the strokes or steps of a peristaltic infusion pump. And, preferably, the control circuitry functions are accomplished using Icnown microprocessor programming techniques to perform the steps described.
  • the bubble detector hardware may still continue to generate a signal indicating air when a nominal three-eighths inch (i.e., fifty microliter ⁇ ) air bubble moves between the transmitter 31 and the receiver 32.
  • the microprocessor 24 continues to advance the infusion pump 16 while counting the number of advancements from the time bubble detector output first decreased to the air/no-air threshold.
  • the microprocessor continues to infuse the liquid until either the air in the line clears the bubble detector 17 before the air bubble advances "X" steps, where "X" is computed as the number of motor advances indicative of an unacceptable size air bubble, or until the infusion pump 16 advances "X” steps without the air in the line clearing the bubble detector 17.
  • the microprocessor stops the infusion pump 16 and activates the alarm 25.
  • Various attributes of the infusion system may affect the determination of "X.” As an example, assume a linear peristaltic pump with the following attributes:
  • a suitable infusion conduit with precision length and internal diameter yielding a volume constant of 1637 steps per milliliter of fluid.
  • ARS volume pumped per active region step
  • the general equation for detecting an "N" microliter air bubble can be derived from the above and expressed in terms of "X" active region steps (ARS) . In that regard, material is normally only moved through the infusion conduit during active region steps. That assumes that the infusion system can properly distinguish between motor pulses in the deadband and motor pulses in the active regions.
  • ARS active region steps
  • N lL 50 tL + (X ARS) (1.0181 ⁇ L/ARS)
  • That value can be set in the programming employed.
  • the microprocessor can be calculated by the microprocessor to reflect a sensitivity level inputted by an operator of the infusion system.
  • known error analysis techniques and empirical methods may be employed to account for system parameters that may affect "X.”
  • the invention provides an infusion device having control circuitry configured to determine if during the time an air bubble is detected the air bubble advances a distance indicative of an unacceptable bubble size. That enables use of a fixed-length bubble detector in a way that can provide reduced sensitivity. In addition, it avoids incurring the cost and inconvenience of modifying the hardware, and the infusion device can be configured to enable operator adjustment of sensitivity level using front panel controls.

Abstract

An infusion device includes an infusion pump for delivering a liquid through an infusion conduit from a separate source of the liquid into a patient, a bubble detector for detecting the presence of an air bubble in the infusion conduit, and control circuitry responsive to the bubble detector for determining if the size of the air bubble is unacceptable. The control circuitry is configured to determine if during the time the air bubble is detected it advances a distance indicative of the unacceptable size, one embodiment counting the steps of a linear peristaltic infusion pump for that purpose.

Description

Apparatus And Method For The Detection Of Air In Fluid Delivery Systems
Background of the Invention Technical Field This invention relates generally to medical equipment, and more particularly to a system and methodology for detecting air in a liquid being delivered into a patient.
Background Information An infusion system for delivering a drug or other liquid into a patient often includes an infusion device that operates to deliver the liquid at an adjustable rate or dosage. Commonly housed in a small cabinet suitable for bedside use, the infusion device operates to control the flow of liquid through a flexible tubing or other infusion conduit that extends from an IV bag or other source of the liquid to an IV needle or other cannula inserted in the patient. In addition to a linear peristaltic infusion pump, the infusion device may include microprocessor control circuitry, front panel operator controls, a display, and an alarm, with those things being integrated in a very functional unit designed to improve intravenous drug administration.
In order to guard against air bubbles flowing into the patient, the infusion device may also include an air detector. Sometimes called a bubble detector, it may take the form of an ultrasonic transmitter/receiver pair and related circuitry arranged to sense air bubbles in the infusion conduit. For that purpose, the ultrasonic transmitter and receiver occupy facing positions on opposite sides of the infusion conduit so that ultrasonic energy passes through the infusion conduit in traveling from the transmitter to the receiver. Whenever an air bubble (i.e., a column of air) moves within the infusion conduit to a position between the transmitter and receiver, it causes :recognizable variation n the receiver output (i.e., bubble detector output) and if that variation is sufficient to signify an air bubble of unacceptable size, control circuitry stops the infusion pump and activates the alarm.
Unacceptable air bubble size may differ, however, and so it would be advantageous to have some way to set that value. Then an operator could select a bubble size most appropriate for a particular infusion situation and that would, among other things, avoid the nuisance alarms accompanying too sensitive a setting. But existing infusion devices often use fixed-length bubble detector schemes so that sensitivity is fixed at some predetermined value such as a three-eighths inch bubble length (i.e., about fifty microliters in some commonly used infusion conduit) .
One common configuration includes a transmitter and receiver about five-eighths inch long and circuitry configured to pass one-eighth inch long bubbles while stopping three-eighth inch bubbles. The circuitry can recognize variations in bubble detector output from a predetermined threshold value signifying that air between the transmitter and receiver is interrupting 20% of the five-eighths inch bubble detector length (i.e., a one-eighth inch long air bubble) , to a predetermined maximum value indicating 60% interruption (i.e., a three-eighths inch long air bubble) . When a three-eighths inch long bubble is detected, the control circuitry stops the infusion pump.
So, infusion device sensitivity to air bubble size (i.e., the acceptable air bubble size) is not adjustable. In addition, minimum sensitivity (i.e., maximum acceptable air bubble size) is dependent on the length of the transmitter/receiver pair, a longer transmitter/receiver pair being required to detect longer air bubbles and establish a threshold value much greater than three-eighths inch. But changing the transmitter/receiver pair and associated hardware may be quite costly and inconvenient. So, some other way is needed to reduce infusion device sensitivity in order to pass air bubbles up to an unacceptable size that is larger than the fixed threshold value, and perhaps even larger than the limit imposed by the length of the transmitter/receiver pair.
Summary of the Invention
This invention solves the problems outlined above by providing an infusion device having control circuitry configured to determine if during the time an air bubble is detected it advances a distance indicative of an unacceptable size. Preferably, that is done with a suitably programmed microprocessor that counts the steps of the infusion pump and compares it with a predetermined .value calculated for the particular infusion device and infusion conduit employed. Thus, the infusion device uses a fixed-length bubble detector in a way that can provide reduced sensitivity, and it does so without incurring the cost and inconvenience of modifying the hardware. In addition, the infusion device can be configured to enable operator adjustment of sensitivity level using front panel controls.
Generally, an infusion device constructed according to the invention includes an infusion pump for delivering a liquid through an infusion conduit from a separate source of the liquid into a patient, a bubble detector for detecting the presence of an air bubble in the infusion conduit, and control means responsive to the bubble detector for determining if the size of the air bubble is unacceptable. According to a major aspect of the invention, the control means is configured to determine if during the time the air bubble is detected it advances a distance indicative of the unacceptable size. Preferably, the control means includes suitably programmed microprocessor circuitry configured to monitor operation of the infusion pump in order to determine the distance the air bubble advances during the time it is detected. In the case of a linear peristaltic infusion pump, for example, the microprocessor counts the steps of the infusion pump as an indication of the distance the air bubble advances and compares it to a value calculated for the particular infusion device and infusion conduit employed. If an unacceptable size is indicated, the microprocessor stops the infusion pump and activates the alarm.
In line with the above, a method of detecting an air bubble of unacceptable size in an infusion conduit through which liquid is to be delivered into a patient includes the step of providing an infusion device having an infusion pump for delivering the liquid through the infusion conduit and a bubble detector arranged to detect the presence of an air bubble in the liquid. The method proceeds by determining if during the time the air bubble is detected it advances a distance indicative of the unacceptable size. Preferably, the step of determining if the air bubble advances a distance indicative of the unacceptable size includes monitoring infusion pump operation, and that may be done with microprocessor circuitry conf gured to count the steps of a linear peristaltic infusion pump.
Brief Description of the Drawings
FIGURE 1 of the drawings is a diagrammatic representation of an infusion device constructed according to the invention; FIGURE 2 is a diagrammatic representation showing details of an air bubble advancing within the infusion conduit between the ultrasonic transmitter and receiver of the bubble detector;
- FIGURE 3 is a representation of a plot of bubble detector output showing how it may vary as the infusion pump advances the air bubble; and
FIGURES A-4C combine to form a flow chart showing the methodology employed to assess air bubble size.
Description of the Preferred Embodiments
Fig. 1 shows an infusion device 10 constructed according to the invention. It operates to deliver a drug or other liquid from a separate source 11 through an infusion conduit 12 to a cannula 13 and into a patient 14. Including some sort of cabinet or other housing depicted in Fig. 1 by the dashed lines 15, the infusion device 10 operates conventionally in many respects and may include many of the features described in U.S. Patent No. 4,648,869 to Bobo, Jr. That patent is incorporated by reference for the details of construction provided.
An infusion pump 16, preferably a linear peristaltic infusion pump, functions conventionally in many respects as infusion pump means for delivering the liquid through the infusion conduit 12. A bubble detector 17, preferably an ultrasonic bubble detector, functions conventionally in many respects as bubble detector means -7-
for detecting the presence of an air bubble in the infusion conduit 12. And a compliment of electronic components, including an amplifier 21, signal conditioning circuitry 22, an analog-to-digital converter 23, and a microprocessor 24, function as ' control means responsive to the bubble detector means for determining if the size of the air bubble is unacceptable (i.e., assessing bubble size).
Similar to the control circuitry in some existing infusion devices, the control circuitry in the infusion device 10 may be configured to stop the infusion pump 16 and activate an alarm 25 in the event an air bubble of unacceptable size is detected. But unlike existing devices, the control circuitry in the infusion device 10 is configured to monitor the distance an air bubble advances in the infusion conduit 12 as an indication of its size. Preferably, that-is done by suitably programming the microprocessor 24 using known programming techniques to perform the steps subsequently described in greater detail.
With the control circuitry so configured, the sensitivity of the infusion device to bubble size (i.e., the unacceptable bubble size threshold) can be set at a selected level. Preferably, that is done with microprocessor programming, and the programming in one embodiment of the invention is so configured that an operator can vary the sensitivity to any of various levels using front panel controls. In addition, the -8-
programming is preferably configured to enable the operator to define the sensitivity level in terms of either bubble length (e.g., nine-sixteenths inch) or bubble volume (e.g., seventy-five microliters) . Besides being adjustable, sensitivity is independent of bubble detector size. In other words, the sensitivity of the infusion device 10 (i.e., the unacceptable bubble size threshold) can be set to a greater value than can be done with existing fixed-length bubble detectors, even to a value corresponding to an air bubble longer than the bubble detector. Those things are possible because the control circuitry of .the infusion device 10 monitors the distance the air bubble advances in the infusion conduit 12 as the air bubble is causing certain variations in the output of the bubble detector 17. That distance taken in conjunction with the inside diameter of the infusion conduit 12, provides sufficient information for the control circuitry to assess the length of the air bubble (i.e., determine whether the size of the air bubble is unacceptable) .
Fig. 2 is a diagrammatic representation showing the advance of an air bubble 30 (i.e., a column of air) in the infusion conduit 12. Dimensions are exaggerated for illustrative convenience. The air bubble 30 advances between an ultrasonic transmitter/receiver pair that includes an ultrasonic transmitter 31 and an ultrasonic receiver 32 that are components of the bubble detector 17 shown in Fig. 1. They are arranged in a known way so that ultrasonic energy passes through the infusion conduit 12 in traveling from the transmitter 31 to the receiver 32. As for the air bubble 30, it has a forward end 33, a rearward end 34, and a length (Lg) that is the distance between the forward end 33 and the rearward end 34 (Fig. 2). Of course, the air bubble 30 can be something other than air, and so it is intended that the term "air bubble" include a column of any other substance that might be detected by the bubble detector 17. As the air bubble 30 approaches the transmitter 31 and receiver 32, the forward end 33 eventually passes to a position between the transmitter 31 and receiver 32 where it causes the bubble detector output to vary in some respect, such as amplitude, from an uninterrupted value indicating that there is only liquid between the transmitter 31 and receiver 32 (point A in Fig. 3) to an air/no-air threshold value indicating the initial presence of the forward end 33 of the air bubble 30 (point B) . That position can be referred to as a first detectable position, and it is illustrated in Fig. 2 by the position occupied by the forward end 33 of the air bubble 30. It may occur, for example, when the forward end 33 of the air bubble 30 extends one-eighth inch between the transmitter 31 and the receiver 32, as depicted by the dimension in Fig. 2 labelled I_T1 (the first threshold) . That represents an interruption of 20% of the five-eighths inch length of the transmitter 31 and receiver 32 (i.e., the bubble detector length labelled LD in Fig. 2) .
For the air bubble 30 illustrated in Fig. 2, the air bubble length Lg is less than the bubble detector length LQ. Thus, as the air bubble 30 continues to advance, the bubble detector output remains constant to point D where the air bubble begins to pass from between the transmitter 31 and the receiver 32. If Lg were equal to or greater than p, however, the bubble detector output would decrease further to a fully interrupted value less than the value at point C.
At point D in Fig. 3, the bubble detector output begins to increase back to the air/no-air threshold value at point E equal to that at point B. That may be called a second or final detectable position and it is depicted in Fig. 2 by an air bubble 30' in phantom lines. It may occur, for example, when one-eighth inch of the air bubble 30' is still between the transmitter 31 and the receiver 32 as depicted by the dimension in Fig. 2 labelled L^ (the second threshold). Then, as the air bubble 30' passes fully beyond the transmitter 31 and the receiver 32, the bubble detector output increases back to an uninterrupted value at point F equal to that at point A. Thus, the bubble detector output varies predictably according to the position of the air bubble 30 between the transmitter 31 and the receiver 32 so that monitoring the distance the air bubble advances from the time the bubble detector output varies from point B to point E in Fig. 3, enables the control circuitry to assess air bubble size. According to one aspect of the invention, that distance is monitored by counting the steps of the infusion pump 16. Then, the number of steps to occur (labeled "X" steps in Fig. 3) is compared with a predetermined value indicative of an unacceptable bubble length.
As is apparent from the foregoing and subsequent descriptions, that can be accomplished by suitably programming the microprocessor 24 according to known programming techniques. The flow chart shown in Figs. 4A-4C provides an example of the steps involved. First, a periodic timer interrupt used to advance the stepper motor of the infusion pump 16 causes program control to proceed to point 40 in Fig. 4A, the start of a pump interrupt service routine. Then the program reads the bubble detector output at 41, examines a SENSOR STATE flag at 42 to determine if it is equal to NO-AIR, and if NO-AIR it is not, the program proceeds to point A in Fig. 4B (subsequently described) .
If the SENSOR STATE flag does equal NO-AIR, the program checks at 43 to see if the bubble detector output is less than the air/no-air threshold level. If it is not, the stepper motor is advanced to the next step at 44 and the program exits the pump interrupt service routine at 45. If the bubble detector output is less than the air/no-air threshold level, the program sets the SENSOR STATE flag at 46 to indicate AIR, advances the stepper motor at 47, and exits the pump interrupt service routine at 48.
Considering now Fig. 4B, the program proceeds from point A to see at 49 if the bubble detector output is less than the air/no-air threshold..,. If. it. is, .the . program checks at 50 to see if the infusion pump 16 is not in the deadband region of the peristaltic pump. If NO, program control proceeds to point B in Fig. 4C. If YES, the program first increments an active region step counter at 51 and then proceeds to point B in Fig. 4C.
If the determination at 49 is NO, the program sets the SENSOR STATE flag to equal NO-AIR at 52. Then, it advances the stepper motor to the next step at 53 and exits the pump interrupt service routine 54.
Considering now Fig. 4C, the program proceeds from point B to see at 55 if the active region step counter is equal or greater than X (the predetermined number of steps indicative of an unacceptable bubble size) . If YES, the program stops the infusion pump and activates the alarm at 56 and exits the pump interrupt service routine at 57. If NO, the program first advances the stepper motor to the next step at 58 and the exits the pump interrupt service routine at 59. Thus, by monitoring the distance the air bubble 30 advances in the infusion conduit as the air bubble 30 causes variations in bubble detector output, the control circuitry determines whether the size of the air bubble 30 is unacceptable. Preferably, the control circuitry monitors infusion pump operation for that purpose, counting the strokes or steps of a peristaltic infusion pump. And, preferably, the control circuitry functions are accomplished using Icnown microprocessor programming techniques to perform the steps described.
In order to ensure timely reading of the bubble detector, its state should be read each time the infusion pump is advanced. The bubble detector hardware may still continue to generate a signal indicating air when a nominal three-eighths inch (i.e., fifty microliterε) air bubble moves between the transmitter 31 and the receiver 32. However, instead of stopping the infusion pump 16 and activating the alarm 25 as may be done in existing infusion devices, the microprocessor 24 continues to advance the infusion pump 16 while counting the number of advancements from the time bubble detector output first decreased to the air/no-air threshold. Then, the microprocessor continues to infuse the liquid until either the air in the line clears the bubble detector 17 before the air bubble advances "X" steps, where "X" is computed as the number of motor advances indicative of an unacceptable size air bubble, or until the infusion pump 16 advances "X" steps without the air in the line clearing the bubble detector 17. In the second case, the microprocessor stops the infusion pump 16 and activates the alarm 25. Various attributes of the infusion system may affect the determination of "X." As an example, assume a linear peristaltic pump with the following attributes:
1. A stepper motor controlled pump mechanism with 200 steps per revolution.
2.. An eight roller linear peristaltic mechanism with 5-degrees angular travel between the top dead center of adjacent rollers.
3. 1 4-degrees (80 motor steps) of deadband region during which no net displacement of fluid takes place.
4. 216-degrees (120 motor steps) of active region during which fluid is actively moved through the fluid path.
5. A suitable infusion conduit with precision length and internal diameter (e.g., 100 mils) yielding a volume constant of 1637 steps per milliliter of fluid.
6. Fifty icroliters of air equals a bubble length of three-eighths inch, assuming a non-pressurized system.
Then, the volume pumped per stroke (or revolution) is derived as
Stroke volume - (200 steps/rev)/(1637 steps/ml) «= 0.122175 ml/rev
and it follows that the volume pumped per active region step (ARS) is derived as
Volume/step = (0.122175 ml/rev)/(120 ARS/rev) = 1.0181 microliter/ARS The general equation for detecting an "N" microliter air bubble can be derived from the above and expressed in terms of "X" active region steps (ARS) . In that regard, material is normally only moved through the infusion conduit during active region steps. That assumes that the infusion system can properly distinguish between motor pulses in the deadband and motor pulses in the active regions. The general equations is
N lL = 50 tL + (X ARS) (1.0181 ^μL/ARS)
Solving for "X" yields a general expression of the number of active region motor steps for a N^μL bubble.
That value can be set in the programming employed.
Alternatively, it can be calculated by the microprocessor to reflect a sensitivity level inputted by an operator of the infusion system. Of course, known error analysis techniques and empirical methods may be employed to account for system parameters that may affect "X."
Thus, the invention provides an infusion device having control circuitry configured to determine if during the time an air bubble is detected the air bubble advances a distance indicative of an unacceptable bubble size. That enables use of a fixed-length bubble detector in a way that can provide reduced sensitivity. In addition, it avoids incurring the cost and inconvenience of modifying the hardware, and the infusion device can be configured to enable operator adjustment of sensitivity level using front panel controls.

Claims

1. An infusion device, comprising: infusion pump means for delivering a liquid through an infusion conduit from a separate source of the liquid into a patient; bubble detector means for detecting the presence of an air bubble in the infusion conduit; and control means responsive to the bubble detector means for determining if the size of the air bubble is unacceptable; which control means is configured to determine if during the time the air bubble is detected it advances a distance indicative of the unacceptable size.
2. An infusion device as recited in Claim 1, wherein the control means is configured to monitor operation of the infusion pump in order to determine the distance the air bubble advances during the time it is detected.
3. An infusion device as recited in Claim 1, wherein the infusion pump is a linear peristaltic infusion pump and the control means is configured to count the steps of the infusion pump as an indication of the distance the air bubble advances.
4. An infusion device as recited in Claim 1, wherein the control means includes microprocessor circuitry.
5. An infusion device as recited in Claim 1, wherein the control means is configured to stop the infusion pump if the size of the air bubble is unacceptable.
6. An infusion device as recited in Claim 1, wherein the control means is configured to activate an alarm if the size of the air bubble is unacceptable.
7. An infusion device as recited in Claim 1, wherein the bubble detector means includes an ultrasonic bubble detector.
8. An infusion device as recited in Claim 7, wherein the ultrasonic bubble detector is a fixed-length bubble detector.
9. A method of detecting an air bubble of unacceptable size in an infusion conduit through which liquid is being delivered into a patient, the method comprising: providing an infusion device having an infusion pump for delivering the liquid through the infusion conduit and a bubble detector arranged to detect the presence of an air bubble in the infusion conduit; determining if during the time the air bubble is detected it advances a distance indicative of the unacceptable size.
10. A method as recited in Claim 9, wherein the step of determining if the air bubble advances a distance indicative of the unacceptable size includes monitoring infusion pump operation.
11. A method as recited in Claim 9, wherein the step of providing includes providing an infusion device having a linear peristaltic infusion pump and the step of determining if the air bubble advances a distance indicative of the unacceptable size includes counting the steps of the infusion pump.
EP91905285A 1990-02-27 1991-02-18 Apparatus for the detection of air in fluid delivery systems Expired - Lifetime EP0470235B1 (en)

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US07/485,720 US4981467A (en) 1990-02-27 1990-02-27 Apparatus and method for the detection of air in fluid delivery systems
US485720 1990-02-27
PCT/US1991/001043 WO1991012848A1 (en) 1990-02-27 1991-02-18 Apparatus and method for the detection of air in fluid delivery systems

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Families Citing this family (118)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH061152Y2 (en) * 1989-04-28 1994-01-12 シャープ株式会社 Infusion pump air detector
JPH06501870A (en) * 1991-06-10 1994-03-03 バクスター、インターナショナル、インコーポレイテッド Intravenous metering monitoring device
JP3138065B2 (en) * 1991-09-04 2001-02-26 シャープ株式会社 Sampling method of bubble detector in infusion device
US5569181A (en) * 1993-10-28 1996-10-29 Medrad, Inc. Sterility assurance for contrast delivery system
DE1258262T1 (en) * 1993-10-28 2003-04-10 Medrad Inc Contrast delivery system
US5827219A (en) * 1993-10-28 1998-10-27 Medrad, Inc. Injection system and pumping system for use therein
EP0650738B1 (en) * 1993-10-28 2003-05-02 Medrad, Inc. Multi-patient fluid dispensing
EP0692766B1 (en) * 1994-07-12 2002-05-08 Medrad, Inc. Closed loop information path for medical fluid delivery systems
US5840026A (en) * 1994-09-21 1998-11-24 Medrad, Inc. Patient specific dosing contrast delivery systems and methods
SE508374C2 (en) * 1995-09-12 1998-09-28 Gambro Med Tech Ab Method and apparatus for detecting the condition of a blood vessel access
US5843035A (en) * 1996-04-10 1998-12-01 Baxter International Inc. Air detector for intravenous infusion system
US6142008A (en) * 1998-06-12 2000-11-07 Abbott Laboratories Air bubble sensor
US6231320B1 (en) 1998-06-12 2001-05-15 Abbott Laboratories Drug infusion pumping cassette latching mechanism
US6554791B1 (en) * 1999-09-29 2003-04-29 Smisson-Cartledge Biomedical, Llc Rapid infusion system
AU2001278187A1 (en) * 2000-07-07 2002-01-21 Fluidsense Corporation Method and apparatus for determining air content and pressure of a liquid in an infusion line
US6489896B1 (en) 2000-11-03 2002-12-03 Baxter International Inc. Air in-line sensor for ambulatory drug infusion pump
US7147615B2 (en) 2001-06-22 2006-12-12 Baxter International Inc. Needle dislodgement detection
US7109974B2 (en) * 2002-03-05 2006-09-19 Matsushita Electric Industrial Co., Ltd. Remote control system including an on-screen display (OSD)
US10155082B2 (en) 2002-04-10 2018-12-18 Baxter International Inc. Enhanced signal detection for access disconnection systems
US7022098B2 (en) 2002-04-10 2006-04-04 Baxter International Inc. Access disconnection systems and methods
US20040254513A1 (en) * 2002-04-10 2004-12-16 Sherwin Shang Conductive polymer materials and applications thereof including monitoring and providing effective therapy
US7052480B2 (en) 2002-04-10 2006-05-30 Baxter International Inc. Access disconnection systems and methods
US7138088B2 (en) * 2002-04-10 2006-11-21 Baxter International Inc. Access disconnection system and methods
WO2004016305A1 (en) * 2002-08-15 2004-02-26 Chang-Ming Yang Drip infusion device
US8029454B2 (en) 2003-11-05 2011-10-04 Baxter International Inc. High convection home hemodialysis/hemofiltration and sorbent system
US7338470B2 (en) * 2003-12-03 2008-03-04 Ethicon Endo-Surgery, Inc. Air-bubble-monitoring medication assembly, medical system and method
CN101084036B (en) 2004-11-16 2011-10-26 梅德拉股份有限公司 System and method for determining transmission function of patients and performing model to response patients of drug infusions
HUE038724T2 (en) 2004-11-24 2018-11-28 Bayer Healthcare Llc Devices and systems for fluid delivery
US7563248B2 (en) 2005-03-17 2009-07-21 Smisson-Cartledge Biomedical Llc Infusion fluid heat exchanger and cartridge
US7975491B2 (en) * 2005-03-17 2011-07-12 Smisson-Cartledge Biomedical Llc Heat exchange system for a pump device
DE102005025500B3 (en) * 2005-06-03 2006-10-05 Fresenius Medical Care Deutschland Gmbh Monitoring presence of air in flowing liquid such as blood, by determining number of sequential time intervals in which amplitude of received ultrasound signal is less than reference level
EP2462882B1 (en) 2006-10-04 2016-12-28 Boston Scientific Limited Interventional catheters
WO2008085421A2 (en) 2006-12-29 2008-07-17 Medrad, Inc. Patient-based parameter generation systems for medical injection procedures
US8631683B2 (en) * 2007-02-06 2014-01-21 Fresenius Medical Care Holdings, Inc. Dialysis systems including non-invasive multi-function sensor systems
US7661293B2 (en) 2007-02-06 2010-02-16 Cosense, Inc. Ultrasonic system for detecting and quantifying of air bubbles/particles in a flowing liquid
US7661294B2 (en) 2007-09-21 2010-02-16 Cosense, Inc. Non-invasive multi-function sensor system
US10463778B2 (en) 2007-02-09 2019-11-05 Baxter International Inc. Blood treatment machine having electrical heartbeat analysis
US8152751B2 (en) 2007-02-09 2012-04-10 Baxter International Inc. Acoustic access disconnection systems and methods
EP2170165B1 (en) 2007-07-17 2018-12-05 Bayer Healthcare LLC Systems for determination of parameters for a procedure, for estimation of cardiopulmonary function and for fluid delivery
US7981082B2 (en) * 2007-08-21 2011-07-19 Hospira, Inc. System and method for reducing air bubbles in a fluid delivery line
US8197431B2 (en) * 2007-09-21 2012-06-12 Baxter International Inc. Acoustic access disconnect detection system
US8062008B2 (en) * 2007-09-27 2011-11-22 Curlin Medical Inc. Peristaltic pump and removable cassette therefor
US7934912B2 (en) * 2007-09-27 2011-05-03 Curlin Medical Inc Peristaltic pump assembly with cassette and mounting pin arrangement
US8083503B2 (en) * 2007-09-27 2011-12-27 Curlin Medical Inc. Peristaltic pump assembly and regulator therefor
US8517990B2 (en) 2007-12-18 2013-08-27 Hospira, Inc. User interface improvements for medical devices
AU2009262505B2 (en) 2008-06-26 2014-08-07 Gambro Lundia Ab Method and device for processing a time-dependent measurement signal
US8192388B2 (en) 2008-07-25 2012-06-05 Baxter International Inc. System and method for detecting access disconnection
US8114043B2 (en) 2008-07-25 2012-02-14 Baxter International Inc. Electromagnetic induction access disconnect sensor
US9421330B2 (en) * 2008-11-03 2016-08-23 Bayer Healthcare Llc Mitigation of contrast-induced nephropathy
CA2766262C (en) 2009-06-26 2018-11-20 Gambro Lundia Ab Devices, a computer program product and a method for data extraction
CA2767007C (en) 2009-07-01 2017-11-21 Fresenius Medical Care Holdings, Inc. Drug delivery devices and related systems and methods
CN102686252B (en) 2009-12-28 2017-01-11 甘布罗伦迪亚股份公司 Apparatus and method for prediction of rapid symptomatic blood pressure decrease
US9151646B2 (en) 2011-12-21 2015-10-06 Deka Products Limited Partnership System, method, and apparatus for monitoring, regulating, or controlling fluid flow
CA2803169C (en) 2010-06-24 2020-09-22 Medrad, Inc. Modeling of pharmaceutical propagation and parameter generation for injection protocols
WO2012106174A1 (en) 2011-01-31 2012-08-09 Fresenius Medical Care Holdings, Inc. Preventing over-delivery of drug
US9987406B2 (en) 2011-02-08 2018-06-05 Fresenius Medical Care Holdings, Inc. Magnetic sensors and related systems and methods
US8353870B2 (en) 2011-04-26 2013-01-15 Fresenius Medical Care Holdings, Inc. Medical temperature sensors and related systems and methods
US8836519B2 (en) 2011-05-12 2014-09-16 Fresenius Medical Care Holdings, Inc. Determining the absence or presence of fluid in a dialysis system
US9333286B2 (en) 2011-05-12 2016-05-10 Fresenius Medical Care Holdings, Inc. Medical tubing installation detection
CA2844807C (en) 2011-08-19 2022-07-26 Hospira, Inc. Systems and methods for a graphical interface including a graphical representation of medical data
ES2770578T3 (en) 2011-08-19 2020-07-02 Icu Medical Inc Pattern Recognition System and Method for Detecting Clogged Fluid Droplets in a Fluid Delivery Path of an Infusion System
US9700672B2 (en) 2011-09-21 2017-07-11 Bayer Healthcare Llc Continuous multi-fluid pump device, drive and actuating system and method
AU2012315820B2 (en) * 2011-09-30 2016-09-29 Icu Medical, Inc. Froth detection system and method
US10022498B2 (en) 2011-12-16 2018-07-17 Icu Medical, Inc. System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy
US10488848B2 (en) 2011-12-21 2019-11-26 Deka Products Limited Partnership System, method, and apparatus for monitoring, regulating, or controlling fluid flow
US10228683B2 (en) 2011-12-21 2019-03-12 Deka Products Limited Partnership System, method, and apparatus for monitoring, regulating, or controlling fluid flow
US9372486B2 (en) 2011-12-21 2016-06-21 Deka Products Limited Partnership System, method, and apparatus for monitoring, regulating, or controlling fluid flow
US9746094B2 (en) 2011-12-21 2017-08-29 Deka Products Limited Partnership Flow meter having a background pattern with first and second portions
US9435455B2 (en) 2011-12-21 2016-09-06 Deka Products Limited Partnership System, method, and apparatus for monitoring, regulating, or controlling fluid flow
US9746093B2 (en) 2011-12-21 2017-08-29 Deka Products Limited Partnership Flow meter and related system and apparatus
US9724467B2 (en) 2011-12-21 2017-08-08 Deka Products Limited Partnership Flow meter
JP6306566B2 (en) 2012-03-30 2018-04-04 アイシーユー・メディカル・インコーポレーテッド Air detection system and method for detecting air in an infusion system pump
US9144646B2 (en) 2012-04-25 2015-09-29 Fresenius Medical Care Holdings, Inc. Vial spiking devices and related assemblies and methods
HUE056182T2 (en) 2012-05-14 2022-01-28 Bayer Healthcare Llc Systems and methods for determination of pharmaceutical fluid injection protocols based on x-ray tube voltage
US9408968B2 (en) * 2012-06-24 2016-08-09 Zevex, Inc. Method and apparatus for detection and management of air-in-line
ES2743160T3 (en) 2012-07-31 2020-02-18 Icu Medical Inc Patient care system for critical medications
US9327072B2 (en) * 2012-12-13 2016-05-03 Zyno Medical, Llc Multifunction capacitive sensor for medical pump
US9759343B2 (en) 2012-12-21 2017-09-12 Deka Products Limited Partnership Flow meter using a dynamic background image
US9555379B2 (en) 2013-03-13 2017-01-31 Bayer Healthcare Llc Fluid path set with turbulent mixing chamber, backflow compensator
US9895109B2 (en) 2013-03-20 2018-02-20 Gambro Lundia Ab Monitoring of cardiac arrest in a patient connected to an extracorporeal blood processing apparatus
WO2014190264A1 (en) 2013-05-24 2014-11-27 Hospira, Inc. Multi-sensor infusion system for detecting air or an occlusion in the infusion system
ES2838450T3 (en) 2013-05-29 2021-07-02 Icu Medical Inc Infusion set that uses one or more sensors and additional information to make an air determination relative to the infusion set
AU2014274122A1 (en) 2013-05-29 2016-01-21 Icu Medical, Inc. Infusion system and method of use which prevents over-saturation of an analog-to-digital converter
USD749206S1 (en) 2013-11-06 2016-02-09 Deka Products Limited Partnership Apparatus to control fluid flow through a tube
USD745661S1 (en) 2013-11-06 2015-12-15 Deka Products Limited Partnership Apparatus to control fluid flow through a tube
USD751690S1 (en) 2013-11-06 2016-03-15 Deka Products Limited Partnership Apparatus to control fluid flow through a tube
USD751689S1 (en) 2013-11-06 2016-03-15 Deka Products Limited Partnership Apparatus to control fluid flow through a tube
USD752209S1 (en) 2013-11-06 2016-03-22 Deka Products Limited Partnership Apparatus to control fluid flow through a tube
JP6636442B2 (en) 2014-02-28 2020-01-29 アイシーユー・メディカル・インコーポレーテッド Infusion systems and methods utilizing dual wavelength optical in-pipe air detection
AU2015266706B2 (en) 2014-05-29 2020-01-30 Icu Medical, Inc. Infusion system and pump with configurable closed loop delivery rate catch-up
JP6336361B2 (en) * 2014-09-05 2018-06-06 テルモ株式会社 Extracorporeal circulation device
US11344668B2 (en) 2014-12-19 2022-05-31 Icu Medical, Inc. Infusion system with concurrent TPN/insulin infusion
AU2016205275B2 (en) 2015-01-09 2020-11-12 Bayer Healthcare Llc Multiple fluid delivery system with multi-use disposable set and features thereof
US10850024B2 (en) 2015-03-02 2020-12-01 Icu Medical, Inc. Infusion system, device, and method having advanced infusion features
CN113598720A (en) 2015-09-25 2021-11-05 C·R·巴德股份有限公司 Catheter assembly with monitoring function
US10413654B2 (en) 2015-12-22 2019-09-17 Baxter International Inc. Access disconnection system and method using signal metrics
USD905848S1 (en) 2016-01-28 2020-12-22 Deka Products Limited Partnership Apparatus to control fluid flow through a tube
CA3013046A1 (en) 2016-01-28 2017-08-03 Deka Products Limited Partnership Apparatus for monitoring, regulating, or controlling fluid flow
WO2017152036A1 (en) 2016-03-03 2017-09-08 Bayer Healthcare Llc System and method for improved fluid delivery in multi-fluid injector systems
EP3454922B1 (en) 2016-05-13 2022-04-06 ICU Medical, Inc. Infusion pump system with common line auto flush
USD854145S1 (en) 2016-05-25 2019-07-16 Deka Products Limited Partnership Apparatus to control fluid flow through a tube
CA3027176A1 (en) 2016-06-10 2017-12-14 Icu Medical, Inc. Acoustic flow sensor for continuous medication flow measurements and feedback control of infusion
US11598664B2 (en) 2017-08-31 2023-03-07 Bayer Healthcare Llc Injector pressure calibration system and method
US11786652B2 (en) 2017-08-31 2023-10-17 Bayer Healthcare Llc System and method for drive member position and fluid injector system mechanical calibration
EP3676854A1 (en) 2017-08-31 2020-07-08 Bayer Healthcare LLC Fluid path impedance assessment for improving fluid delivery performance
US11478581B2 (en) 2017-08-31 2022-10-25 Bayer Healthcare Llc Fluid injector system volume compensation system and method
AU2018326379B2 (en) 2017-08-31 2024-03-21 Bayer Healthcare Llc Method for dynamic pressure control in a fluid injector system
JP2018038891A (en) * 2017-12-14 2018-03-15 株式会社根本杏林堂 Portable injection device and control method for portable injection device
US10089055B1 (en) 2017-12-27 2018-10-02 Icu Medical, Inc. Synchronized display of screen content on networked devices
CN108362830A (en) * 2018-01-15 2018-08-03 湖北民族学院 The SCM Based infusion atmospheric monitoring system of one kind and method
USD964563S1 (en) 2019-07-26 2022-09-20 Deka Products Limited Partnership Medical flow clamp
WO2021021596A1 (en) 2019-07-26 2021-02-04 Deka Products Limited Partnership Apparatus for monitoring, regulating, or controlling fluid flow
ES2933693T3 (en) * 2019-11-18 2023-02-13 Eitan Medical Ltd Rapid test for medical pump
US11278671B2 (en) 2019-12-04 2022-03-22 Icu Medical, Inc. Infusion pump with safety sequence keypad
WO2022020184A1 (en) 2020-07-21 2022-01-27 Icu Medical, Inc. Fluid transfer devices and methods of use
US11135360B1 (en) 2020-12-07 2021-10-05 Icu Medical, Inc. Concurrent infusion with common line auto flush
US11920581B2 (en) 2021-01-29 2024-03-05 Masterflex Llc Flow rate control for pump with flow sensor
US11846279B2 (en) 2021-01-29 2023-12-19 Masterflex, Llc Accurate volume dispensing using pump and flow sensor

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4565500A (en) * 1983-02-24 1986-01-21 Stewart-Riess Laboratories, Inc. Air bubble detecting and discriminating circuit arrangement and method
WO1989001796A1 (en) * 1987-08-28 1989-03-09 Bellhouse Technology Limited Bubble detector

Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4496346A (en) * 1983-08-17 1985-01-29 Air-Shields, Inc. Infusion monitoring apparatus
AU4536685A (en) * 1984-08-06 1986-02-13 Abbott Laboratories Optical drop detecting system
IT1179808B (en) * 1984-10-31 1987-09-16 Hospal Dasco Spa DETECTION AND CONTROL EQUIPMENT FOR THE PRESENCE OF A GASEOUS FLUID IN CORRESPONDENCE WITH A PREFIXED LEVEL OF A LIQUID CONTAINER
US4658244A (en) * 1985-03-28 1987-04-14 Imed Corporation Air-in-line detector
SE459641B (en) * 1986-03-24 1989-07-24 Gambro Ab DETECTOR SYSTEM CONTROLS A BLOOD CIRCULATION ALTERNATIVE WITH A SIGNIFICANTLY UNLESSED
FR2599496B1 (en) * 1986-05-28 1992-02-14 Mms BUBBLE DETECTOR IN A LIQUID CIRCUIT
US4762518A (en) * 1986-08-01 1988-08-09 Pancretec, Inc. Blockage hazard alarm in an intravenous system
JPH076946B2 (en) * 1986-08-22 1995-01-30 株式会社日立製作所 Air bubble detector
US4764166A (en) * 1987-08-17 1988-08-16 Fisher Scientific Company Ultrasonic air-in-line detector
JPH01198560A (en) * 1988-02-03 1989-08-10 Meteku:Kk Detector for detecting pressure of pipe transport fluid and air bubble contained therein
JPH0255957U (en) * 1988-10-15 1990-04-23

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4565500A (en) * 1983-02-24 1986-01-21 Stewart-Riess Laboratories, Inc. Air bubble detecting and discriminating circuit arrangement and method
WO1989001796A1 (en) * 1987-08-28 1989-03-09 Bellhouse Technology Limited Bubble detector

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of WO9112848A1 *

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DE69114073T2 (en) 1996-05-30
EP0470235B1 (en) 1995-10-25
MX174109B (en) 1994-04-21
US4981467A (en) 1991-01-01
WO1991012848A1 (en) 1991-09-05
IL97206A0 (en) 1992-05-25
AU7348491A (en) 1991-09-18
BR9104685A (en) 1992-05-19
DK0470235T3 (en) 1995-12-04
KR0157986B1 (en) 1998-11-16
DE69114073D1 (en) 1995-11-30
CA2051703A1 (en) 1991-08-28
KR920700716A (en) 1992-08-10
CA2051703C (en) 1997-10-14
JPH04505412A (en) 1992-09-24
ATE129415T1 (en) 1995-11-15
ZA911209B (en) 1991-11-27
AU632910B2 (en) 1993-01-14
JP3321620B2 (en) 2002-09-03
EP0470235A4 (en) 1992-12-16

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